WO2014057394A1 - Imagerie spectrale quantitative - Google Patents

Imagerie spectrale quantitative Download PDF

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Publication number
WO2014057394A1
WO2014057394A1 PCT/IB2013/059060 IB2013059060W WO2014057394A1 WO 2014057394 A1 WO2014057394 A1 WO 2014057394A1 IB 2013059060 W IB2013059060 W IB 2013059060W WO 2014057394 A1 WO2014057394 A1 WO 2014057394A1
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WO
WIPO (PCT)
Prior art keywords
energy
display
spectral image
measurement
image
Prior art date
Application number
PCT/IB2013/059060
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English (en)
Inventor
Roland Proksa
Original Assignee
Koninklijke Philips N.V.
Philips Deutschland Gmbh
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Koninklijke Philips N.V., Philips Deutschland Gmbh filed Critical Koninklijke Philips N.V.
Priority to EP13780413.4A priority Critical patent/EP2906121A1/fr
Priority to CN201380052863.7A priority patent/CN104736059A/zh
Priority to JP2015535151A priority patent/JP2015532140A/ja
Priority to BR112015007654A priority patent/BR112015007654A2/pt
Priority to US14/433,750 priority patent/US20150248782A1/en
Priority to RU2015117461A priority patent/RU2015117461A/ru
Publication of WO2014057394A1 publication Critical patent/WO2014057394A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4007—Arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units
    • A61B6/4014—Arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units arranged in multiple source-detector units
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T11/00—2D [Two Dimensional] image generation
    • G06T11/60—Editing figures and text; Combining figures or text
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4241—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using energy resolving detectors, e.g. photon counting
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/46—Arrangements for interfacing with the operator or the patient
    • A61B6/461—Displaying means of special interest
    • A61B6/463—Displaying means of special interest characterised by displaying multiple images or images and diagnostic data on one display
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/48—Diagnostic techniques
    • A61B6/482—Diagnostic techniques involving multiple energy imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
    • A61B6/5217—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data extracting a diagnostic or physiological parameter from medical diagnostic data
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T5/00—Image enhancement or restoration
    • G06T5/50—Image enhancement or restoration using two or more images, e.g. averaging or subtraction
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T5/00—Image enhancement or restoration
    • G06T5/70—Denoising; Smoothing
    • G—PHYSICS
    • G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H50/00—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics
    • G16H50/30—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics for calculating health indices; for individual health risk assessment
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10004—Still image; Photographic image
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10072—Tomographic images
    • G06T2207/10081—Computed x-ray tomography [CT]
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/20—Special algorithmic details
    • G06T2207/20212—Image combination
    • G06T2207/20221—Image fusion; Image merging

Definitions

  • CT computed tomography
  • a typical CT scanner has included an x-ray tube mounted on a rotatable gantry opposite a detector.
  • the x-ray tube rotates around an examination region and emits polychromatic radiation that traverses the examination region and a subject and/or object disposed therein.
  • the detector array detects radiation that traverses the examination region and produces a signal indicative thereof.
  • a reconstructor reconstructs the signal and generates volumetric image data indicative of the subject and/or object disposed in the examination region.
  • One or more images can be generated from the volumetric image data.
  • Existing image data analysis software applications include tools that determine information from a displayed image. For example, tools exist that allow the user to measure a distance between two points in a displayed image, measure a noise level for a predefined region of interest in a displayed image, measure an average attenuation value
  • the measured attenuation values in a CT scan show variations (e.g., due to the polychromatic emission spectrum) and thus cannot be considered as quantitative information.
  • Spectral CT scanners can overcome this.
  • Examples of spectral CT scanners include scanners with energy switching x-ray tubes, multiple x-ray tubes, scanners with multiple detector layers, and scanner with photon counting detectors.
  • energy-dependent decomposition techniques can be used to generate quasi mono-chromatic images.
  • Scanners with multiple detector layers and/or photon counting detectors have an inherent ability to produce quasi mono energetic images.
  • these images represent the attenuation of a mono energetic beam at a specific energy and include information that represents a physical quantity.
  • the quasi mono energetic images will contain unwanted noise.
  • the noise will depend on the selected x-ray tube energy, the spectral properties of the scanner, and the imaging protocol.
  • a clear noise minimum can be obtained at a particular energy level as the optimum (or minimum noise) level may vary and therefore might not correspond to mono energy level for measurement reporting.
  • a method in one aspect, includes generating a first measurement spectral image from first spectral image data based on a predetermined energy. The method further includes determining a first measurement value for a first region of interest in the first measurement spectral image. The method further includes overlying the first measurement value in connection with a corresponding first region of interest in a visually presented first display spectral image, wherein the energy is different from a first display energy of the first display spectral image.
  • a system in another aspect, includes a reconstructor that generates a measurement spectral image from spectral image data based on a measurement energy.
  • the system further includes a measurement energy identifier that determines a first measurement value for a first region of interest in the measurement spectral image.
  • the system further includes a rendering engine that overlays the first measurement value in connection with a corresponding first region of interest in a visually presented first display spectral image, wherein the measurement energy is different from a first energy of the first display spectral image.
  • a computer readable storage medium is encoded with computer readable instructions.
  • the computer readable instructions when executed by a processer, causes the processor to: generate a first measurement spectral image from first spectral image data based on a predetermined measurement energy, determine a first measurement value for a first region of interest in the first measurement spectral image, and overlay the first measurement value in connection with a corresponding first region of interest in a visually presented first display spectral image, wherein the measurement energy is different from a first display energy of the first display spectral image.
  • the invention may take form in various components and arrangements of components, and in various steps and arrangements of steps.
  • the drawings are only for purposes of illustrating the preferred embodiments and are not to be construed as limiting the invention.
  • FIGURE 1 schematically illustrates an example imaging system in connection with a processing device.
  • FIGURE 2 illustrates an example method for displaying measurements in connection with an image.
  • FIGURE 3 schematically illustrates an example dual layer detector.
  • FIGURE 4 schematically illustrates another example dual layer detector.
  • FIGURE 5 schematically illustrates a multi-radiation source imaging system.
  • FIGURE 6 schematically illustrates a detector array with a photon-counting detector and corresponding processing electronics.
  • a measurement for a region of interest identified in a displayed spectral image is calculated based on the same region of interest in a different but corresponding spectral image.
  • a same image data set can be used to generate multiple spectral images, each for a different energy, a first spectral image for a first engery can be displayed whereas a CT number measurement overlaid over the first spectral image for a region of interest identified in the first spectral image is determined based on a second spectral image for a second different energy.
  • this allows a user to scroll through the different energy images and select a spectral image to display for observation or chose a default spectral image such as the spectral image with a lowest noise level or highest contrast level to display for observation while measurement calculations are made using a same spectral image, rendering the measurement independent of the energy of the displayed spectral image and/or providing an energy normalized measurement that can be compared with other measurements calculated from a same energy image.
  • an imaging system 100 includes a computed tomography (CT) scanner, which includes a generally stationary gantry portion 102 and a rotating gantry portion 104.
  • the rotating gantry portion 104 is rotatably supported by the generally stationary gantry portion 102 via a bearing (not visible) or the like.
  • a radiation source 106 such as an x-ray tube, is supported by the rotating gantry portion 104 and rotates therewith around an examination region 108 about a longitudinal or z-axis.
  • a radiation source voltage controller 110 controls a target (mean or peak) emission voltage of the radiation source 106. In one instance, this includes switching the emission voltage between two or more emission voltages (e.g., 80 keV and 140 keV, 80 kV, 100 keV and 120 keV, etc.) between views of a scan, within a view of a scan, and/or otherwise. As a result, radiation beams with different energy spectra may be used to scan a subject/object in a same scan.
  • emission voltages e.g. 80 keV and 140 keV, 80 kV, 100 keV and 120 keV, etc.
  • a detector array 1 12 subtends an angular arc opposite the examination region 108 relative to the radiation source 106.
  • the detector array 1 12 detects radiation that traverses the examination region 108 and generates a signal indicative thereof.
  • the scan is a multiple energy beam scan and the radiation source voltage is switched between at least two emission voltages for a scan, the detector array 1 12 generates a signal, d combat (where n is an integer value corresponding to a particular energy), for each of the radiation source voltages.
  • d where n is an integer value corresponding to a particular energy
  • a couch or subject support 1 14 supports a subject or object in the examination region 108.
  • the support 1 14 positions the subject or object in the examination region 108 before, during and/or after scanning.
  • An operator console 1 16 facilitates user interaction with the scanner 100.
  • software applications executed by the operator console 1 16 allows a user to select an imaging protocol such as an imaging protocol that includes switching the radiation source emission voltage for a scan, select a spectral reconstruction algorithm, initiate scanning, etc.
  • a processing device 1 18 processes the signals dminister. It is to be appreciated that the processing device 1 18 includes one or more micro-processors that execute one or more computer readable instructions to implement the below discussed functionality performed thereby. In one instance, the one or more computer readable instructions are encoded on computer readable storage medium such a physical memory and/or other non-transitory medium. Additionally or alternatively, a computer readable instruction can be carried by a carrier waver, a signal and/or other transitory medium.
  • the illustrated processing device 1 18 includes a reconstructor 120 that reconstructs the signals d combat and generates volumetric image data.
  • the reconstructor 120 can employs one or more spectral decomposition algorithms 122 and/or other spectral reconstruction algorithms.
  • the reconstructor 120 employs a decomposition algorithm that models the signals as a combination of the photo-electric effect with attenuation spectrum P(E) and the Compton effect with attenuation spectrum C(E).
  • Equation 1 The density length product for these components, namely, that of the photoelectric effect component p and the Compton effect component c, in each signal d n can be modeled as a non-linear system according to the relationship: Equation 1 :
  • d n J dE T(E) D n (E)exp(- (p P(E) + c C(E))), where T(E) is the emission spectrum of the radiation source 106 and D n (E) is the spectral sensitivity of the nth measurement.
  • T(E) is the emission spectrum of the radiation source 106
  • D n (E) is the spectral sensitivity of the nth measurement.
  • results, p and c can be used alone or in combination to reconstruct images of a desired energy component using known and/or other reconstruction algorithms.
  • Sensitivity and noise robustness may generally be improved by, for example, increasing the number of energy ranges.
  • the reconstructor 120 reconstructs the signals d n into individual images, using image based analysis algorithms.
  • One non-limiting approach is to perform an N-dimensional cluster analysis to decompose the images into components such as soft tissue, calcium, iodine or other materials, where N is the number of distinct spectral measurements performed for each geometric ray.
  • a display 124 visually presents one or more spectral images for one or more different energy levels.
  • the display 124 visually presents the one or more spectral images in connection with an interactive graphical user interface (GUI), which includes software based tools that can be activated through icons and/or other graphical indicia presented in the GUI with an input signal from an input device 126 such as a keyboard, a mouse, a touch screen, etc.
  • GUI graphical user interface
  • tools may include visualization tools (e.g., window/level, zoom, pan, rotate, etc.), measurements tools (e.g., CT number, length, noise, etc.), and/or other tools.
  • An image energy identifier 128 identifies the energy level for displayed image.
  • the image energy identifier 128 can employ a default image energy 130, one or more calculated energy 132, or an energy specified in an input signal from the input device 126.
  • the image energy identifier 128 may first use the default image energy 130.
  • the default image energy 130 may be determined by the manufacturer of the display software application, a clinical imaging site, a group of clinical experts, a standardization body, and/or otherwise.
  • the input device 126 can then be used to select a particular calculated energy 132.
  • the one or more calculated energies 132 are each visually presented via the display 124 as activateable software icons (e.g., buttons, menus items, or the like).
  • the user uses the input device 126 to activate a desired one of the one or more calculated energies 132, for example, via mouse.
  • An example calculated energy corresponds to the energy resulting in an image with a least amount of noise or an image with a highest contrast material level.
  • the energy specified in the input signal from the input device 126 can be a particular value such as an energy value entered at the keypad of a keyboard input device 126, selected by a mouse input device 126 through a menu of predefined values, etc.
  • the software icon can present a graphical slider which maps each slider position to a different energy. In this instance, the user can slide the slider using the input device 126 to dynamically change the energy identified for presenting the image.
  • a measurement energy identifier 134 identifies an energy value for the image which is used to take measurements such as determine an average CT number of a region of interest of the displayed image.
  • the measurement energy identifier 134 can employ a default measurement energy 136 (or, optionally, an energy specified in an input signal from the input device 126).
  • the measurement energy identifier 134 may in general use a default measurement energy 136 that corresponds to a regional, national and/or international standardized energy and/or other energy.
  • the energy valued identified by the image energy identifier is the energy valued identified by the image energy identifier
  • the energy identified by the measurement energy identifier 134 are different values.
  • the energy corresponding to a particular noise level or contrast material level may vary between scans, scanned objects and/or subjects, etc.
  • the image energy value determined by the image energy identifier 128 may vary from study to study.
  • the default measurement energy 136 may remain the same. This allows the user to select a spectral image at any energy for display while calculating measurements at the same energy, which provides an energy normalized measurement.
  • the particular energy value can also be displayed and/or made otherwise available.
  • the particular energy value can be displayed and/or made otherwise available. For instance, when determining an average CT number for a region of interest, the displayed measurement value may be presented as: "100 HU at 65keV", even though the displayed image is not a 65 keV image.
  • Using a standardized measurement energy value for calculating measurements is well suited for applications in which images and measurements are compared, e.g., pre and post tumor treatment images, because a change in a measurement between two images will not be a function of a change in the energy.
  • FIGURE 2 illustrates an example method for visually presenting an image and calculating and overlaying a measurement for a region of interests identified in the visually presented image.
  • a spectral scan is performed, producing an image data set that can be used to generate one or more images for one or more different energy levels.
  • an energy is identified for a display image.
  • a spectral image at the identified energy is generated, producing the display image, and displayed.
  • a region of interest is identified in the displayed display spectral image for a measurement.
  • a measurement energy which is different from the display image energy, is obtained.
  • a spectral image at the measurement energy is generated, producing a measurement image corresponding to the display image.
  • the measurement is calculated based on the region of interest and the measurement image.
  • the measurement is overlaid over the display image in connection with the identified region of interest.
  • the measurement energy is optionally displayed along with the overlaid measurement.
  • the above may be implemented by way of computer readable instructions, encoded or embedded on computer readable storage medium, which, when executed by a computer processor(s), cause the processor(s) to carry out the described acts. Additionally or alternatively, at least one of the computer readable instructions is carried by a signal, carrier wave or other transitory medium.
  • FIGURES 3 and 4 schematically illustrate variations in which the detector array 112 includes multi-layer energy-resolving detectors.
  • This detector array 112 may be used in configurations which of the system 100 with and without the radiation source voltage controller 110.
  • the detector array 112 includes a dual layer detector with a first layer 302 of a first scintillation material having a first thickness 304 and a second layer 306 of a second scintillation material having a second thickness 308.
  • the first and second scintillator layers 302 and 306 are stacked in a configuration in which the first layer 302 is closer to impinging radiation 310.
  • First and second photo-sensors 312 and 314 are arranged next to each other along a direction transverse to the stacking of the scintillator 302 and 306 and under the stacked scintillators 302 and 306, relative to the direction of the incoming radiation.
  • Energy absorption is dependent on the thickness of the material(s) used to form the first and second scintillation layers 302 and 306.
  • the thickness 304 of the first layer 302 is thinner relative to the thickness 308 of the second layer 306.
  • the thicknesses 304 and 308 may be equal or the thickness 304 may be thinner than the thickness 308.
  • the spectral separation generally, is given by the fact that the first layer absorbs the low energy photons, which have higher absorption likelihood than high energy photons.
  • the photo-sensors 312 and 314 have emission spectra that match to the spectral sensitivities of the corresponding scintillation layers 302 and 306. As a result, only the light emitted by the first scintillation layer 302 is absorbed by the first photo-sensor 312, and only the light emitted by the second scintillation layer 306 is absorbed by the second photo-sensor 314.
  • the photo-sensors 312 and 314 respectively detect the light produced by the first and second layers 302 and 306 and generate and output different signals
  • FIGURE 4 shows a variation of FIGURE 3 in which the photo-sensors 312 and 314 are stacked in a direction of the impinging radiation 310 and arranged parallel to the stacked scintillators 302 and 306 in a direction perpendicular to the impinging radiation 310.
  • a light reflective coating 402 may be included on surfaces of the first and second layers 302 and 306 to respectively direct light to the photo-sensors 312 and 314.
  • first and second layers 302 and 306 generate and output different signals corresponding to the spectral sensitivities of the corresponding scintillation layers 302 and 306.
  • FIGURE 5 schematically illustrates a variation of the system 100 that includes multiple radiation sources 106i, ..., 106N (where N is an integer) and corresponding detector arrays 112 l s ..., 112 N . Each source/detector pair generates and outputs a signal having different spectral characteristics.
  • This multi-radiation source configuration may be used in configurations with the detector arrays 112 of FIGURES 1, 3 and/or 4 and/or in
  • FIGURE 6 schematically illustrates a variation in which the detector array 112 includes photon counting detectors.
  • the detector array 112 generates a signal, such as an electrical current or voltage signals, having a peak amplitude that is indicative of the energy of a detected photon, and processing electronics 600 identify and/or associates the detected photon with an energy range corresponding to the energy of the detected photon for the detected photon based on the signal.
  • the processing electronics 600 includes a pulse shaper 602 that processes the signal and generates a pulse such as voltage or other pulse indicative of the energy of the detected photon.
  • An energy-discriminator 604 energy discriminates the pulse.
  • the energy-discriminator 604 includes multiple comparators 606. Each comparator 606 receives the pulse and compares a peak amplitude of the pulse to an energy level threshold. A comparator 606 produces an output indicative of whether the amplitude exceeds the corresponding threshold.
  • a counter 608 increments a count value for each threshold based on the output of the energy-discriminator 604.
  • a binner 610 energy bins the signals and, hence, the photons into two or more energy ranges or windows based on the counts. For example, a bin may be defined for the energy range between two thresholds. In this instance, the
  • reconstructor 120 selectively reconstructs the signals generated by the detector 112 based on the spectral characteristics of the signals.

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Abstract

L'invention concerne un procédé qui consiste à générer une première image spectrale de mesure à partir de premières données d'image spectrale sur la base d'une énergie de mesure prédéterminée. Le procédé consiste en outre à déterminer une première valeur de mesure pour une première région d'intérêt dans la première image spectrale de mesure. Le procédé consiste en outre à superposer la première valeur de mesure en liaison avec une première région d'intérêt correspondante dans une première image spectrale d'affichage présentée visuellement, l'énergie de mesure étant différente d'une première énergie d'affichage de la première image spectrale d'affichage.
PCT/IB2013/059060 2012-10-09 2013-10-02 Imagerie spectrale quantitative WO2014057394A1 (fr)

Priority Applications (6)

Application Number Priority Date Filing Date Title
EP13780413.4A EP2906121A1 (fr) 2012-10-09 2013-10-02 Imagerie spectrale quantitative
CN201380052863.7A CN104736059A (zh) 2012-10-09 2013-10-02 定量谱成像
JP2015535151A JP2015532140A (ja) 2012-10-09 2013-10-02 スペクトル画像診断のための方法及びシステム
BR112015007654A BR112015007654A2 (pt) 2012-10-09 2013-10-02 método e sistema
US14/433,750 US20150248782A1 (en) 2012-10-09 2013-10-02 Quantitative spectral imaging
RU2015117461A RU2015117461A (ru) 2012-10-09 2013-10-02 Количественная спектральная визуализация

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US201261711559P 2012-10-09 2012-10-09
US201261711428P 2012-10-09 2012-10-09
US61/711,428 2012-10-09
US61/711,559 2012-10-09

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EP (1) EP2906121A1 (fr)
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CN (1) CN104736059A (fr)
BR (1) BR112015007654A2 (fr)
RU (1) RU2015117461A (fr)
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